Implantable battery device for standard cochlear implant

ABSTRACT

An implantable battery device is disclosed, which comprises a battery, a first antenna, a second antenna, and a driving unit. The first antenna is configured to inductively supply energy from the battery to a first device and to transmit information received from a processing unit to the first device. The second antenna is provided for wireless communication with a second device. The driving unit is configured to operate the first antenna according to control signals received from the processing unit. The processing unit is configured to transmit control signals to the driving unit to control the inductive supply of energy to the first device, to receive information via the second antenna from the second device, and to transmit information received via the second antenna from the second device to the first device via the first antenna driven by the driving unit.

This application is a Continuation of copending application Ser. No.16/557,744, filed on Aug. 30, 2019, which claims priority under 35U.S.C. § 119(a) to application Ser. No. 18/191,951.5, filed in Europe onAug. 31, 2018, all of which are hereby expressly incorporated byreference into the present application.

FIELD

The present disclosure relates to an implantable battery device. Moreparticularly, the disclosure relates to implantable battery device foruse with a standard cochlear implant that can be used as a wirelessrelay device for audio signals.

BACKGROUND

Cochlear implants for assisting users having hearing disabilities areknown. Current cochlear implant systems are composed by an externaldevice (called BTE device, “Behind The Ear” device or sound processor)and an implantable device (called “cochlear implant”). Typically, acochlear implant is implanted into the head of the user and comprises areceiver coil and an electrode. The electrode is implanted close to thecochlea and provides stimuli to the cochlea of the user, while thereceiver coil is implanted at a position in the head of the user at therear side of the head, where it can be wirelessly connected to anexternal transmitter coil.

The transmitter coil generates an alternating electromagnetic field,which inductively transmits information and energy to the receiver coilof the cochlear implant. The transmitter coil is connected to theBehind-the-ear hearing aid device, which provides e.g. a microphone, abattery, and a sound processor for processing audio signals recorded bythe microphone, for processing the audio signals according topredetermined processing and settings, and providing the processed audiosignals (information) and energy from the battery to the cochlearimplant using the link between the transmitter coil and the receivercoil.

However, since there is biological tissue between the receiver coil andthe transmitter coil, the transmission of energy to the receiver coilcan heat up the biological tissue between the coils and in the vicinityof the coils, thus causing a damage to the tissue and/or causing anuncomfortable feeling to the user. Therefore, in order to lower themagnetic field strength, the coils are made to be relatively large, thuscausing an aesthetic issue for the user. Even though the coils arearranged e.g. to be covered by hair and are typically arranged on thebackside of the head of the user, there is still an uncomfortablefeeling to the user of the hearing aid due to the large transmitter coilbeing placed visibly on the backside of the head of the user.

It is known that a part of the deafness community does not want to weara cochlear implant because of the large size of the external device(processor and antenna on the skull).

Therefore, there is a need to provide a solution that addresses at leastsome of the above-mentioned problems. The present disclosure provides atleast an alternative to the prior art.

SUMMARY

According to an aspect of the application, an implantable battery deviceis provided, which comprises a battery, a first antenna, a secondantenna, and a driving unit. The first antenna is configured to supplyenergy inductively from the battery to a first device and to transmitinformation received from a processing unit to the first device. Thesecond antenna is provided for wireless communication with a seconddevice. The driving unit is configured to operate the first antennaaccording to control signals received from the processing unit. Theprocessing unit is configured to transmit control signals to the drivingunit to control the inductive supply of energy to the first device, toreceive information via the second antenna from the second device, andto transmit information received via the second antenna from the seconddevice to the first device via the first antenna driven by the drivingunit.

The implantable battery device of the present invention allows fortransmitting information from the second device to the implantablebattery device, thus removing the need of using large coils for thetransmission of energy from the second device. Since the energy foroperating the first device is taken from the implantable battery device,the energy does not have to be transmitted from the second device.Hence, the second device can be made smaller, while also the secondantenna can be made smaller than the first antenna, since only dataneeds to be transmitted. Hence, the aesthetic appearance can be mademore attractive to users.

Further, the driving unit may be configured to control an amplitude ofan electromagnetic field emitted from the first antenna according tocontrol signals received from the processing unit.

This allows for the processing unit to control the amount of energy thatis being transmitted to the first device. Hence, the battery lifetimecan be prolonged.

Furthermore, the driving unit may be configured to modulate theamplitude and/or a frequency of the electromagnetic field emitted fromthe first antenna according to the information received from theprocessing unit.

This allows for controlling the second antenna for transmission ofenergy and information to the first device. Furthermore, the informationcan be efficiently transferred, while also the transmission of energycan be improved.

In addition, the processing unit may be configured to transmitinformation to the second device via the second antenna.

This allows for sending back information to the second device. Suchinformation may include for example information on the status of thefirst device. When the information is further transmitted to a devicehaving a user interface such as a SmartPhone, the user can in this waytake notice of certain parameters of the first device or the implantablebattery device.

Further, the processing unit may be configured to obtain a charge stateof the battery, and to control the inductive supply of energy to thefirst device depending on the charge state.

This allows stopping the energy transfer process in case a certain lowerthreshold of the battery charge state is underrun, for example. Further,this allows reducing the amount of transferred energy depending oncertain parameters.

Furthermore, the first antenna may comprise a magnetically interactingpart in a center of the first antenna for alignment of the first antennawith at least one other antenna.

Some implanted devices comprise an antenna having a magnet for aligningan external device to the antenna of the implanted device. Hence, amagnetically interacting part may improve the efficiency of thecoupling, while it further allows to waive extra fixing means.Alternatively, a magnet may be provided on the first antenna, henceallowing to improve a coupling efficiency to an external device.

In addition, the processing unit may be configured to control theinductive supply of energy to the first device depending on informationreceived by the second device.

This allows to control the transmission of energy to the first devicedepending on a user interaction, for example.

Further, the battery may be a rechargeable battery, and the implantablebattery device may further comprise a battery charging unit, which isconfigured to receive energy via the first antenna from another devicefor recharging the battery.

This allows for extending the lifetime of the implantable batterydevice. Hence, less surgery is required for a user for changing theimplant or the battery, hence improving a comfort for the user.

Furthermore, the first device may be a cochlear implant, and the seconddevice may be a hearing aid sound processor.

Even further, the processing unit may be configured to processinformation from the hearing aid sound processor to be transmitted tothe cochlear implant.

This allows for applying the above-described benefits to hearingdevices, especially cochlear implants. Using the described implantablebattery device, existing cochlear implants can be retrofitted so thatthe aesthetic appearance can be improved for existing users of cochlearimplants.

According to another aspect of the application, a hearing aid soundprocessor is provided, which is configured to transmit audio signals toan implantable battery device according to any one of the above aspectsusing a wireless link.

This allows for providing a dedicated sound processor, which can besmaller in size due to a reduction in battery capacity, hence being moreattractive for users to wear.

According to yet another aspect of the application, a charging device isprovided, which is configured to charge an implantable battery deviceaccording to any one of the above aspects.

This allows for providing of a dedicated charger device, which does notneed to be a sound processor. Indeed, a separate charger device may beprovided, which is attached or connected to the implantable batterydevice only if recharging is required. This further allows to reduce thesize of the external sound processor, as the charging functionality doesnot have to be provided in the sound processor.

The implantable battery device may comprise only a single antennaconfigured to transmit and receive energy and data between the firstdevice and the second device. Thereby, you avoid having two antennas.

BRIEF DESCRIPTION OF DRAWINGS

The aspects of the disclosure may be best understood from the followingdetailed description taken in conjunction with the accompanying figures.The figures are schematic and simplified for clarity, and they just showdetails to improve the understanding of the claims, while other detailsare left out. Throughout, the same reference numerals are used foridentical or corresponding parts. The individual features of each aspectmay each be combined with any or all features of the other aspects.These and other aspects, features and/or technical effect will beapparent from and elucidated with reference to the illustrationsdescribed hereinafter in which:

FIG. 1 illustrates an implantable battery device according to anembodiment of the disclosure;

FIG. 2 illustrates a further implantable battery device according to anembodiment of the disclosure;

FIG. 3A illustrates a schematic communication diagram according to anembodiment of the disclosure;

FIG. 3B illustrates a schematic communication diagram according to anembodiment of the disclosure;

FIG. 4 illustrates a schematic communication diagram according to anembodiment of the disclosure;

FIG. 5A shows a cross-section through an implantable cochlear implantaccording to an embodiment of the disclosure;

FIG. 5B shows a cross-section through another example of an implantablecochlear implant according to an embodiment of the disclosure;

FIG. 5C shows a cross-section through yet another example of animplantable cochlear implant according to an embodiment of thedisclosure;

FIG. 5D shows a cross-section through yet another example of animplantable cochlear implant according to an embodiment of thedisclosure;

FIG. 5E shows a cross-section through yet another example of animplantable cochlear implant according to an embodiment of thedisclosure;

FIG. 5F shows a cross-section through yet another example of animplantable cochlear implant according to an embodiment of thedisclosure;

FIG. 5G shows a cross-section through yet another example of animplantable cochlear implant according to an embodiment of thedisclosure;

FIG. 6A illustrates a sound processor for a cochlear implant of theprior art; and

FIG. 6B illustrates a cochlear implant of the prior art.

DETAILED DESCRIPTION

The detailed description set forth below in connection with the appendeddrawings is intended as a description of various configurations. Thedetailed description includes specific details for the purpose ofproviding a thorough understanding of various concepts. However, it willbe apparent to those skilled in the art that these concepts may bepracticed without these specific details. Several aspects of theapparatus and methods are described by various blocks, functional units,modules, components, circuits, steps, processes, algorithms, etc.(collectively referred to as “elements”). Depending upon particularapplication, design constraints or other reasons, these elements may beimplemented using electronic hardware, computer program, or anycombination thereof.

The electronic hardware may include microprocessors, microcontrollers,digital signal processors (DSPs), field programmable gate arrays(FPGAs), programmable logic devices (PLDs), gated logic, discretehardware circuits, and other suitable hardware configured to perform thevarious functionality described throughout this disclosure. Computerprogram shall be construed broadly to mean instructions, instructionsets, code, code segments, program code, programs, subprograms, softwaremodules, applications, software applications, software packages,routines, subroutines, objects, executables, threads of execution,procedures, functions, etc., whether referred to as software, firmware,middleware, microcode, hardware description language, or otherwise.

A hearing device may include a hearing aid that is adapted to improve oraugment the hearing capability of a user by receiving an acoustic signalfrom a user's surroundings, generating a corresponding audio signal,possibly modifying the audio signal and providing the possibly modifiedaudio signal as an audible signal to at least one of the user's ears.The “hearing device” may further refer to a device such as an earphoneor a headset adapted to receive an audio signal electronically, possiblymodifying the audio signal and providing the possibly modified audiosignals as an audible signal to at least one of the user's ears. Suchaudible signals may be provided in the form of an acoustic signalradiated into the user's outer ear, or an acoustic signal transferred asmechanical vibrations to the user's inner ears through bone structure ofthe user's head and/or through parts of middle ear of the user orelectric signals transferred directly or indirectly to cochlear nerveand/or to auditory cortex of the user.

The hearing device is adapted to be worn in any known way. This mayinclude i) arranging a unit of the hearing device behind the ear with atube leading air-borne acoustic signals into the ear canal or with areceiver/loudspeaker arranged close to or in the ear canal such as in aBehind-the-Ear type hearing aid, and/or ii) arranging the hearing deviceentirely or partly in the pinna and/or in the ear canal of the user suchas in a In-the-Ear type hearing aid or In-the-Canal/Completely-in-Canaltype hearing aid, or iii) arranging a unit of the hearing deviceattached to a fixture implanted into the skull bone such as in BoneAnchored Hearing Aid or Cochlear Implant, or iv) arranging a unit of thehearing device as an entirely or partly implanted unit such as in BoneAnchored Hearing Aid or Cochlear Implant.

A “hearing system” refers to a system comprising one or two hearingdevices, and a “binaural hearing system” refers to a system comprisingtwo hearing devices where the devices are adapted to cooperativelyprovide audible signals to both of the user's ears. The hearing systemor binaural hearing system may further include auxiliary device(s) thatcommunicates with at least one hearing device, the auxiliary deviceaffecting the operation of the hearing devices and/or benefitting fromthe functioning of the hearing devices. A wired or wirelesscommunication link between the at least one hearing device and theauxiliary device is established that allows for exchanging information(e.g. control and status signals, possibly audio signals) between the atleast one hearing device and the auxiliary device.

Such auxiliary devices may include at least one of remote controls,remote microphones, audio gateway devices, mobile phones, public-addresssystems, car audio systems or music players or a combination thereof.The audio gateway is adapted to receive a multitude of audio signalssuch as from an entertainment device like a TV or a music player, atelephone apparatus like a mobile telephone or a computer, a PC. Theaudio gateway is further adapted to select and/or combine an appropriateone of the received audio signals (or combination of signals) fortransmission to the at least one hearing device. The remote control isadapted to control functionality and operation of the at least onehearing devices. The function of the remote control may be implementedin a SmartPhone or other electronic device, the SmartPhone/electronicdevice possibly running an application that controls functionality ofthe at least one hearing device.

In general, a hearing device includes i) an input unit such as amicrophone for receiving an acoustic signal from a user's surroundingsand providing a corresponding input audio signal, and/or ii) a receivingunit for electronically receiving an input audio signal. The hearingdevice further includes a signal processing unit for processing theinput audio signal and an output unit for providing an audible signal tothe user in dependence on the processed audio signal.

The input unit may include multiple input microphones, e.g. forproviding direction-dependent audio signal processing. Such directionalmicrophone system is adapted to enhance a target acoustic source among amultitude of acoustic sources in the user's environment. In one aspect,the directional system is adapted to detect (such as adaptively detect)from which direction a particular part of the microphone signaloriginates. This may be achieved by using conventionally known methods.The signal processing unit may include amplifier that is adapted toapply a frequency dependent gain to the input audio signal. The signalprocessing unit may further be adapted to provide other relevantfunctionality such as compression, noise reduction, etc. The output unitmay include an output transducer such as a loudspeaker/receiver forproviding an air-borne acoustic signal transcutaneously orpercutaneously to the skull bone or a vibrator for providing astructure-borne or liquid-borne acoustic signal. In some hearingdevices, the output unit may include one or more output electrodes forproviding the electric signals such as in a Cochlear Implant.

Patients suffering from deafness or severe to profound hearing losscaused by severe loss of inner ear hair cells are often candidates for acochlear implant solution as depicted in FIGS. 6A and 6B. Currentsolutions consist of an implanted part 640, 650 (the cochlear implant)consisting of an antenna 650 and electronics 640 placed under the skin.

A cochlear implant typically includes i) an external part 600 (so called“Behind the ear” device (BTE device) or sound processor) for picking upby a microphone 610 and processing sound from the environment, and fordetermining sequences of pulses for stimulation of the electrodes 650 independence on the current input sound, ii) a (typically wireless, e.g.inductive) communication link for simultaneously transmittinginformation about the stimulation sequences and for transferring energyto iii) an implanted part 640, 650 (so called implant) allowing thestimulation to be generated and applied to a number of electrodes 650,which are implantable in different locations of the cochlea allowing astimulation of different frequencies of the audible range. That is, thecochlear implant has e.g. an electrode array 650 that is placed in thecochlear with the purpose of stimulating the hearing nerves directlyelectrically. Such systems are e.g. described in U.S. Pat. No. 4,207,441and in U.S. Pat. No. 4,532,930.

In an aspect, the hearing device comprises a multi-electrode array e.g.in the form of a carrier comprising a multitude of electrodes adaptedfor being located in the cochlea in proximity of an auditory nerve ofthe user. The carrier is preferably made of a flexible material to allowproper positioning of the electrodes in the cochlea such that theelectrodes 650 may be inserted in cochlea of a recipient. Preferably,the individual electrodes are spatially distributed along the length ofthe carrier to provide a corresponding spatial distribution along thecochlear nerve in cochlea when the carrier is inserted in the cochlea.

As mentioned above, the external part 600, 620, 630 and the cochlearimplant 640 are both linked by an inductive field in order to deliver,from the sound processor to the implant, the energy for the cochlearimplant and the information for the stimulation. The inductive field istypically generated by an excitation coil 620 (in the following:transmitter coil) and is picked up by a receiver coil 640 connected tothe implant. That is, current systems work with an inductive fieldgenerated by the external antenna, which is configured to deliver thepower and data to the implant.

That is, the outer part consists of a transmitter antenna 620 placedover the implanted antenna 640, which is connected to the soundprocessor 600 placed behind the ear or integrated with the outerantenna. The external part holds one or more relatively large batteriesto supply the sound processor and the cochlear implant 640, 650 throughinductive coupling through the skin.

This kind of architecture has an aesthetic issue for the user as theinductive link is transmitted by a large visible antenna 620 placed onthe patient's skull (e.g. on the rear side of the user's head). Hencewearing a cochlear implant may cause an uncomfortable feeling to theuser, because of the large size of the external device (sound processor600 with antenna part 620 on the skull). In other words, externalcomponents are often very visible due to the size of the antenna 620 andthe large batteries. This is cosmetically not attractive for the users.

The present invention however, provides a new system architecture inorder to reduce the size of the external device 600, 620 and to increaseits aesthetic appearance. Further, the invention is related to a newsystem architecture in order to reduce the external device size andincrease the aesthetic benefit.

In certain embodiments of the invention as depicted in FIGS. 5A to 5G, abattery 510 may be included in the implanted device 500. This allows fortransmitting only data from the external sound processor to the implant,since the energy for the cochlear implant is taken from the battery 510in the implant 500. Hence, the external antenna can be made smaller,which increases the aesthetic appearance of the cochlear implant as awhole.

With a battery 510 included in the implant, only the data must bedelivered to the cochlear implant 500, which reduces the requirementsfor the communication protocol.

However, in the embodiments depicted in FIGS. 5A to 5G, differentembodiments having a battery 510 in the cochlear implant 500 are shown.Note that the embodiments of a generally circular shape are shown.However, the invention is not limited to being circular. FIG. 5A shows across-section through an implantable cochlear implant 500 according toan embodiment of the disclosure. The cochlear implant 500 comprises acoil 520, in the middle of which a battery 510 and a magnet 530 areplaced, for example. The radius or dimension of the magnet 530 shall beequal or larger than the battery 510 in order to shield the battery 510from the electromagnetic field imposed on the cochlear implant 500 by anexternal device (not shown). Furthermore, the magnet 530 may be arrangedon a side of the battery 510 pointing outwards, while the battery 510 isplaced on a side of the magnet 530 towards the skull. Hence, the magnet530 is acting as a shield to protect the battery 510 from theelectromagnetic field indicated by the arrows. The magnetic field may bean alternating magnetic field. Hence, the battery 510 can be shieldedfrom the electromagnetic field which otherwise will induce heat to thebattery 510 due to eddy current heating. Therefore, a lifetime of thebattery 510 can be extended as compared to the unshielded case.

FIG. 5B shows a modification of the embodiment above with the differencethat a shield 540 is configured to shield the battery 510 from unwantedelectromagnetic induction from an external charger device, andadditional shielding elements 545 improve the shielding effect. Suchshield 540 may be placed on the outwards pointing side of the battery510. Hence, the battery 510 can be shielded from the electromagneticfield which otherwise will induce heat to the battery. Therefore, alifetime of the battery 510 can be extended.

FIG. 5C shows a further modification of the embodiment above with thedifference that a shield 540 is configured to shield the battery 510from unwanted electromagnetic induction from an external charger device.However, as opposed to the embodiments above, when the battery 510 isplaced below the coil 520 and the magnet 530, the battery 510 can bemade much larger. The shield 540 can again be placed on the outwardspointing side of the battery 510. Hence, the battery 510 can be shieldedfrom the electromagnetic field which otherwise will induce heat to thebattery 510. Therefore, a lifetime of the battery 510 can be extended.

FIG. 5D shows a further modification of the embodiment above with thedifference that a shield 540 is configured to shield the battery 510from unwanted electromagnetic induction from an external charger device.However, as opposed to the embodiments above, the shield 540 may notextend across the full length of the battery 510, but may have e.g. ahole in the middle. The shield 540 can again be placed on the outwardspointing side of the battery 510. Hence, the battery 510 can be shieldedfrom the electromagnetic field which otherwise will induce heat to thebattery 510. Therefore, a lifetime of the battery 510 can be extended.

FIG. 5E shows a further modification of the embodiment above with thedifference that the battery 510 and a shield 540 are provided in anextra compartment, which is connected by wires to the main housing ofthe cochear implant 500. The radius or dimension of the shield 540 shallbe equal or larger than the battery 510 in order to shield the battery510 from the electromagnetic field. Since the magnetic field will belower at the remote location of the extra compartment, it is againpossible to shield the battery 510 from unwanted electromagneticinduction from an external charger device. The shield 540 may again beplaced on the outwards pointing side of the battery 510. Hence, thebattery 510 can be shielded from the electromagnetic field whichotherwise will induce heat to the battery 510. Therefore, a lifetime ofthe battery 510 can be extended.

FIG. 5F shows a further modification of the embodiment above with thedifference that the battery 510 and a shield 540 are provided in anextra compartment, which is directly connected to the main housing ofthe cochear implant 500. The radius or dimension of the shield 540 shallbe equal or larger than the battery 510 in order to shield the battery510 from the electromagnetic field. Since the magnetic field will belower at the location of the extra compartment, it is again possible toshield the battery 510 from unwanted electromagnetic induction from anexternal charger device. The shield 540 may again be placed on theoutwards pointing side of the battery 510. Hence, the battery 510 can beshielded from the electromagnetic field which otherwise will induce heatto the battery 510. Therefore, a lifetime of the battery 510 can beextended.

FIG. 5G shows a further modification of the embodiment above with thedifference that the battery 510 is provided in an extra compartment,which is arranged on the electrode wire 550 to the cochlea. Since themagnetic field will be lower at the location of the extra compartment,it is again possible to shield the battery 510 from unwantedelectromagnetic induction from an external charger device. Hence, thebattery 510 can be shielded from the electromagnetic field whichotherwise will induce heat to the battery 510. Therefore, a lifetime ofthe battery 510 can be extended.

In certain embodiments of the invention, a temperature sensor mayadditionally be placed on or at the battery. In such a case, thecochlear implant 500 may be configured to transmit the temperature ofthe battery 510 to the external charger via the same coil 520, which isbeing used for charging the battery 510. Hence, the external charger canbe configured to control the charging process according to thetemperature of the battery, so that heating of the battery can be avoidor reduced. Hence, the temperature can be modulated such that the samecoil can be used for both charging and communication at the same time.

In certain embodiments of the invention, the link between the externaldevice and the cochlear implant can be achieved using otherradiofrequency protocols, which may transmit data only.

This allows using other frequencies in a more flexible way, because theefficiency on the radiofrequency in term of transmission of energy canbe neglected for the normal use case. That is, the external device canhave a lower footprint and the antenna can be made smaller and a largerdistance can be achieved from the external antenna to the antenna of theimplant. The use of a wireless communication technology between thesound processor and cochlear implant can use a technology that does nottake up much space, such as a near-link coil, a Bluetooth antenna, orthe like.

The use of a low power radio system (such as near field magnetic) with arange sufficient to reach the contralateral ear allows a single soundprocessor to be placed in one ear to optionally drive two implants(ipsi- and contralateral).

In certain embodiments of the invention, alternating inductive fieldsare used for transmitting energy and/or information. When usingalternating inductive fields, standard electronic components can beused, hence saving costs.

In certain embodiments of the invention, the BTE device may be includedinside an antenna, since no inductive antenna on the skull is necessaryduring normal operation. In this case, the size of the antenna can begreatly reduced, since smaller batteries can be used since no energy ofthe BTE device is used to supply energy to the implant.

In certain embodiments of the invention, the antenna may be includedinside a BTE device, since no inductive antenna on the skull isnecessary during normal operation. In this case, the battery of theexternal sound processor can be greatly reduced, such as e.g. more than70% of the battery size used today, which are used to supply energy tothe implant. Hence, the sound processor can look like a normal hearingaid, which leads to a great benefit for the user. That is, the soundprocessor part can be reduced in size by using a minimal battery sizeand using a form factor that is small enough to be completely or almostcompletely hidden, e.g. in the ear canal (e.g. IIC style).

Having the sound processor for the cochlear implant hidden in the earcanal provides for the benefit, that the sound processor becomes almostinvisible. Furthermore, the sound processor is not in the way, when e.g.combing the hair or wearing glasses. Even more, in case the soundprocessor is placed in the ear canal, the sound processor is more orless protected from direct weather exposure such as rain, snow,sunlight, wind, etc., and external influences, such as high or lowtemperature, high or low humidity, while it is also less exposed toturbulent wind noise. Furthermore, the natural outer ear sound shaping(directionality) is preserved when having the receiving microphonesitting inside the ear canal opening. In addition, the sound processoris fully accessible by the user and hence, allows service, upgrades andreplacements without requiring any surgery or any hardware modificationof the implant. Additionally, the cochlear implant does not require amagnet for holding the external antenna, and can thus be made smaller,slimmer and lighter. Further, the cochlear implant can be placed morefreely as in the case of a closely matching external antenna, whichneeds to transmit energy to the cochlear implant, since fewerrestrictions are imposed on the cochlear implant.

In certain embodiments of the invention, the cochlear implant maycomprise a rechargeable battery. Since the use of a normal battery willlead to a rather short lifetime, and hence to an early replacement ofthe cochlear implant, a rechargeable battery allows for a longerlifetime of the cochlear implant.

Hence, in certain embodiments of the invention, the user may be requiredto recharge the implantable battery device 100 using for example anexternal device, which may be a sound processor having an inductive linkinside and enough batteries to charge the rechargeable battery of theimplant. Thus, the user may install the connection to an inductiveantenna only when it is necessary to recharge the rechargeable batteryof the implant, using e.g. a connector on the sound processor, to whichthe inductive transmitter coil can be connected. From an aesthetic pointof view, the user has the benefit to wear the sound processor behind theear without the large inductive antenna most of the time, since theprocessor does not need to have an inductive link inside in order toimprove the device's aesthetic. Hence, in the normal use case, the largeinductive antenna is not visible, thus providing the advantages of theinvention.

Once, the user wants to recharge the rechargeable battery, the user canconnect the large inductive antenna to a respective connector of thesound processor, and position the large inductive antenna on the rearside of his head over the implanted antenna, and start the rechargingprocess using the batteries in the sound processor as an energy source.

In certain embodiments of the invention, the external part mayoptionally also have a receiver (speaker) implemented for invisiblecombined acoustic and electric stimulation, which effectively makes it ahearing instrument with modified firmware to control also the cochlearimplant via the wireless technology.

Further, in certain embodiments of the invention, the user may also usean external device for charging, which is different from the soundprocessor, that is, another device may be used to charge the battery.For example, the user may use a dedicated charger device, which may be aconnected to the user's skull for example for night-time charging duringsleep of the user. Such a separate inductive charging system for thecochlear implant can be provided e.g. under a pillow in the user's bedfor night charging.

In certain embodiments, such a dedicated charger device may be batterydriven or may be connected to mains power. It can further bemechanically designed such, that the sound processor is included in theantenna and may be used only to charge the battery (very few times inthe day or in the night). This also provides a great aesthetic benefitto the user, since the user does not have to wear the large soundprocessor device all the time.

In order to improve battery lifetime of the cochlear implant, in certainembodiments of the invention, techniques may be applied for reducing theenergy consumption of the implant. With reference to FIG. 4, such atechnique is explained. The cochlear implant needs a minimum voltage inorder to supply the device correctly with energy and to allow a minimumof voltage compliance. The voltage compliance is the minimum voltagenecessary to deliver the desired stimulation current into the patientimpedance 450, i.e. the power supply voltage of the device, whichcorresponds to the possible maximum impedance at the maximum currentavailable.

In order to improve battery lifetime, in certain embodiments of theinvention, an energy source may be implanted, that is, the cochlearimplant may receive energy from another implanted device.

The cochlear implant needs a minimum of voltage in order to supply powerto the device correctly and to allow a minimum of voltage compliance.

The voltage compliance is the minimum voltage necessary to deliver thedesired stimulation pulses to the implanted electrodes 430, 440. Theseelectrodes 430, 440 through being connected to the cochlear of the userrepresent a certain electrical impedance 450. That is, the requiredpower supply voltage of the device corresponds to the maximum impedanceof the electrode array multiplied with the maximum current that isrequired for suitable stimulation.

Since the power supply is usually implemented with a regulator device,depending of the patient having a cochlear implant having certainmaximum current and electrode impedance, a part of the energy isdirectly converted in electrical loss, that is, in heating into thedevice.

As an example, the implant may be powered at 5V, while the parameters ofthe cochlear implant of a user are an impedance of 2 kΩ and a requiredstimulation current of 1 mA. Hence, the minimum power supply toguarantee the stimulation is 2 kΩ×1 mA=2V, which is lower than the 5Vthat are supplied to the cochlear implant. That is, in this example theexternal device sends more energy than is required (here, 3V) andtherefore, the energy storage of the BTE device is used faster.

In order to improve the battery lifetime without any compromise with thevoltage compliance, this user would like to address a loop controlarchitecture from the patient impedance to the implant power supplyaccording to FIG. 4.

This loop is based on a voltage measurement done during the standardstimulation behavior between electrodes 430, 440. The patient'simpedance 450 is calculated during the stimulation based on a sample andhold circuitry 460 which determines a voltage corresponding to theelectrode impedance 450. This voltage is used for example in a voltagecontrolled oscillator circuitry 420 in order to tune the samplingfrequency of a regulator in the Stimulation Engine 400 based on a switchcapacitor 410. Thus, the power supply of the implant, output of theregulator, is tuned as close as possible to the minimum voltagenecessary for the user's voltage compliance.

This loop can be activated for example for each stimulation or between aspecific time, depending of the impedance change or the calculation loadof the implant.

In certain embodiments of the invention, a battery 150 may be providedin an implanted battery device 100 as depicted in FIG. 1. An implantedbattery device 100 needs to be serviceable, replaceable, or removableduring e.g. MRI examination, independently from the rest of the cochlearimplant. Also, in case of a battery failure, the cochlear implant needsto remain functional. Hence, an implantable battery device 100 having abattery 150 may be required not to have a physical connector to thecochlear implant, which is challenging in implantable context. That is,not having a physical connector to an implanted cochlear implant is anadditional benefit due to improved failure safety. Hence, using thepresent embodiment of the invention, any standard cochlear implant maybe transformed into a more implantable solution without the need toremove the implant, which can be particularly useful for pediatricimplantation where implanting a cochlear device having a battery may betoo big for a young user of an cochlear implant, but where the usercould benefit from an implantable battery device later.

Hence, FIG. 1 shows an implantable battery device 100 according to anembodiment of the invention, which is introduced as a third part to acochlear implant system, additional to a cochlear implant (not shown inFIG. 1) and a sound processor (not shown in FIG. 1). The implantablebattery device 100 comprises a first antenna 110 providing an inductivelink to a first device 310, and a second antenna 120 providing awireless link to a second device 320. The first antenna 110 is providedto couple to the inductive antenna of the first device 310, and cantransmit data and energy to the first device 310. The implantablebattery device 100 further features a processing unit 130, and a drivingunit 140.

The implantable battery device 100 is surgically placed next to thefirst device 310, with the first antenna 110 inductively coupled to thereceiving antenna of the first device. The inductive antenna 110 may bemade from a thin and soft material (e.g., electrical wires in silicone).The battery 150 may be e.g. a rechargeable battery or a super capacitor.

FIG. 3A illustrates a schematic communication diagram according to anembodiment of the disclosure. In FIG. 3A, the normal use case isdepicted. An external second device, that is, e.g. a BTE device of acochlear implant system may provide a microphone as well as wirelesscapabilities (wireless link), while it does not need to have aninductive antenna for transmitting energy. The microphone can capturesound and transmit all relevant data (information) to the implantablebattery device 100 via the wireless link via the second antenna 120.With reference to FIG. 1, the processing unit 130 receives theinformation via the second antenna 120, and processes the information tobe suitable for stimulating the electrodes of the cochlear implant. Theprocessing unit 130 sends the processed information to the driving unit140 together with control signals, such as e.g. the amplitude of theelectromagnetic field that is to be generated. The driving unit 140 thendrives the first antenna 110 to generate an inductive field for thetransmission of energy and information to the first device 310 via theinductive link.

In other words, the implantable battery device 100 therefore acts as arelay between the external microphone of the sound processor 320 and thecochlear implant 310: audio information will be received by the cochlearimplant 310 from the microphone in the external part 320 through thewireless link to the implantable battery device 100, while energy andaudio information will be delivered from the implantable battery device100 to the cochlear implant 310 through the implanted inductive firstantenna 110.

That is, an implantable battery device 100 is provided which comprises abattery 150, a first antenna 110, configured to inductively supplyenergy from the battery 150 to a first device 310 (the cochlearimplant), and to transmit information received from a processing unit130 to the first device 310. The implantable battery device 100 furthercomprises a second antenna 120 for wireless communication with a seconddevice 320 (the BTE device), and a driving unit 140, configured tooperate the first antenna 110 according to control signals received fromthe processing unit 130, wherein the processing unit 130 is configuredto transmit control signals to the driving unit 140 to control theinductive supply of energy to the first device 310, receive informationvia the second antenna 120 from the second device 320, and to transmitinformation received via the second antenna 120 from the second device320 to the first device 310 via the first antenna 110 driven by thedriving unit 140.

The driving unit 130 may further be configured to control an amplitudeof an electromagnetic field emitted from the first antenna 110 accordingto control signals received from the processing unit 140. For example,the transmission of energy may be stopped or started depending on thecharge state of the battery 150, or on instructions received from thesecond device 320, e.g. in order to temporarily switch off the cochlearimplant.

The driving unit 130 may further be configured to modulate the amplitudeand/or a frequency of the electromagnetic field emitted from the firstantenna 110 according to the information received from the processingunit 140. The modulation may be matched e.g. to improve an efficiency ofan energy transfer or may depend on parameters of the cochlear implantof the user, such as the impedance of the electrode array.

This solution allows to transform any cochlear implant into a moreimplantable system, without any implanted connector. The implantablebattery device 100 can be removed or replaced with the cochlear implantin place and unaltered, or placed later after the first cochlear implantsurgery. In case of a battery failure or battery replacement (followingbattery failure or MRI examination), this solution avoids all risks forthe cochlear implant.

Furthermore, the battery of the external sound processor can be greatlyreduced, such as e.g. more than 70% of the battery size used today,which are used to supply energy to the implant. Hence, the soundprocessor can look like a normal hearing aid, which leads to a greatbenefit for the user. That is, the sound processor part can be reducedin size by using a minimal battery size and using a form factor that issmall enough to be completely or almost completely hidden, e.g. in theear canal (e.g. IIC style).

Having the sound processor for the cochlear implant hidden in the earcanal provides for the benefit, that the sound processor becomes almostinvisible. Furthermore, the sound processor is not in the way, when e.g.combing the hair or wearing glasses. Even more, in case the soundprocessor is placed in the ear canal, the sound processor is more orless protected from direct weather exposure such as rain, snow,sunlight, wind, etc., and external influences, such as high or lowtemperature, high or low humidity, while it is also less exposed toturbulent wind noise. Furthermore, the natural outer ear sound shaping(directionality) is preserved when having the receiving microphonesitting inside the ear canal opening. In addition, the sound processoris fully accessible by the user and hence, allows service, upgrades andreplacements without requiring any surgery or any hardware modificationof the implant. Additionally, the cochlear implant does not require amagnet for holding the external antenna, and can thus be made smaller,slimmer and lighter. Further, the cochlear implant can be placed morefreely as in the case of a closely matching external antenna, whichneeds to transmit energy to the cochlear implant, since fewerrestrictions are imposed on the cochlear implant.

The inductive antenna 110 of the implantable battery device 100 isplaced on top of the antenna of the cochlear implant 310, thus allowingfor an efficient coupling between the implantable battery device and thecochlear implant.

Furthermore, in case of battery failure or battery discharge, a standardprocessor with external inductive antenna as depicted in FIG. 3B can beused as an emergency alternative by the patient to use his cochlearimplant, with the implantable battery device 100 in a mode where it isbypassed.

To secure the implantable battery device 100 in place, a magnet in themiddle of the inductive antenna can be used, or if the cochlear implantdesign allows it, the removable magnet of the cochlear implant could beintegrated to the inductive antenna 110 of the implantable batterydevice 100 to secure it on top of the cochlear implant. Any otherstandard fixation solution (using sutures, dacron mesh or screws forexample) could be also used as an alternative or in addition.

In certain embodiments, the implantable battery device 100 may have arechargeable battery 150. In such a case, it is required to charge therechargeable battery 150 from time to time.

FIG. 3B shows a situation in which the battery 150 of the implantablebattery device 100 is recharged. An external charger 330 is arranged sothat the first antenna 110 of the implantable battery device 100 canreceive an electromagnetic field generated by the external charger 330.

The implantable battery device 100 as depicted in FIG. 2, additionallycomprises a charging unit 160, which is configured to receive energyfrom the first antenna 110, which picks up energy from an inductivefield generated by an external charger device, thus charging the battery150 of the implantable battery device 100. To control the chargingprocess efficiently, the processing unit 130 may be configured to obtaina charge state of the battery 150. Furthermore, the processing unit maybe configured to control the inductive supply of energy to the firstdevice 310 depending on the charge state. Even further, the processingunit 130 may be configured to transmit information to the second device320 via the second antenna 120 or to the external charger via the secondantenna 320 or via the first antenna 110, such as information on thecharge state of the battery 150.

In such a situation, it is important that the battery 150 is shieldedfrom the electromagnetic field, which otherwise will induce heat intothe battery 150. Such heating will shorten the lifetime of the battery150.

In certain embodiments of the invention, a temperature sensor is placedon or at the battery 150, thus providing the processing unit withinformation on the battery temperature. This information can then betransmitted back to the external charger 330 e.g. via the same firstantenna 110, which is being used for charging the battery. Thetemperature can be modulated such that the same coil can be used forboth charging and communication at the same time.

A Computer Readable Medium

In an aspect, the functions may be stored on or encoded as one or moreinstructions or code on a tangible computer-readable medium. Thecomputer readable medium includes computer storage media adapted tostore a computer program comprising program codes, which when run on aprocessing system causes the data processing system to perform at leastsome (such as a majority or all) of the steps of the method describedabove and in the claims.

By way of example, and not limitation, such computer-readable media cancomprise RAM, ROM, EEPROM, CD-ROM or other optical disk storage,magnetic disk storage or other magnetic storage devices, or any othermedium that can be used to carry or store desired program code in theform of instructions or data structures and that can be accessed by acomputer. Disk and disc, as used herein, includes compact disc (CD),laser disc, optical disc, digital versatile disc (DVD), floppy disk andBlu-ray disc where disks usually reproduce data magnetically, whilediscs reproduce data optically with lasers. Combinations of the aboveshould also be included within the scope of computer-readable media. Inaddition to being stored on a tangible medium, the computer program canalso be transmitted via a transmission medium such as a wired orwireless link or a network, e.g. the Internet, and loaded into a dataprocessing system for being executed at a location different from thatof the tangible medium. For example, the processing in the cochlearimplant to adapt the signals for use with the cochlear implant may berendered in software.

A Data Processing System

In an aspect, a data processing system comprising a processor adapted toexecute the computer program for causing the processor to perform atleast some (such as a majority or all) of the steps of the methoddescribed above and in the claims. For example, the processing in thecochlear implant to adapt the signals for use with the cochlear implantmay also be rendered as a data processing system.

It is intended that the structural features of the devices describedabove, either in the detailed description and/or in the claims, may becombined with steps of the method, when appropriately substituted by acorresponding process.

As used, the singular forms “a,” “an,” and “the” are intended to includethe plural forms as well (i.e. to have the meaning “at least one”),unless expressly stated otherwise. It will be further understood thatthe terms “includes,” “comprises,” “including,” and/or “comprising,”when used in this specification, specify the presence of statedfeatures, integers, steps, operations, elements, and/or components, butdo not preclude the presence or addition of one or more other features,integers, steps, operations, elements, components, and/or groupsthereof. It will also be understood that when an element is referred toas being “connected” or “coupled” to another element, it can be directlyconnected or coupled to the other element but an intervening elementsmay also be present, unless expressly stated otherwise. Furthermore,“connected” or “coupled” as used herein may include wirelessly connectedor coupled. As used herein, the term “and/or” includes any and allcombinations of one or more of the associated listed items. The steps ofany disclosed method is not limited to the exact order stated herein,unless expressly stated otherwise.

It should be appreciated that reference throughout this specification to“one embodiment” or “an embodiment” or “an aspect” or features includedas “may” means that a particular feature, structure or characteristicdescribed in connection with the embodiment is included in at least oneembodiment of the disclosure. Furthermore, the particular features,structures or characteristics may be combined as suitable in one or moreembodiments of the disclosure. The previous description is provided toenable any person skilled in the art to practice the various aspectsdescribed herein. Various modifications to these aspects will be readilyapparent to those skilled in the art, and the generic principles definedherein may be applied to other aspects.

The claims are not intended to be limited to the aspects shown herein,but is to be accorded the full scope consistent with the language of theclaims, wherein reference to an element in the singular is not intendedto mean “one and only one” unless specifically so stated, but rather“one or more.” Unless specifically stated otherwise, the term “some”refers to one or more.

Accordingly, the scope should be judged in terms of the claims thatfollow.

LIST OF REFERENCE SIGNS

-   100 Implantable Battery Device-   110 First Antenna-   120 Second Antenna-   130 Processing Unit-   140 Driving Unit-   150 Battery-   160 Charging Unit-   310 First External Device-   320 Second External Device-   330 External Charger-   400 Stimulation Engine-   410 Switched Capacitor Power Supply-   420 Voltage Controlled Oscillator-   430 Electrode 1-   440 Electrode 2-   450 Impedance-   460 Hold and Sampling-   500 Cochlear Implant-   510 Battery-   520 Magnet Coil-   530 Magnet-   540 Shield-   545 Additional Shielding Element-   550 Electrode Array-   600 Sound Processor-   610 Microphone-   620 External Transmitter Antenna-   630 External Magnet-   640 Internal Magnet, Antenna and Receiver Coil/Stimulator-   650 Electrode

1. Implantable battery device, comprising: a rechargeable battery, afirst antenna, configured to inductively supply energy from the batteryto a first device, and to transmit information received from aprocessing unit to the first device, and inductively supply energy tothe battery from a second device, and a driving unit, configured tocontrol the supply of energy to the first device via the first antennaaccording to control signals received from a processing unit, whereinthe processing unit is configured to generate the control signals forcontrolling the inductive supply of energy to the first device based oninformation received from a third device, said third device beingnon-implanted.
 2. Implantable battery device according to claim 1,further comprising: a second antenna configured to conduct wirelesscommunication with the third device, wherein the processing unit isfurther configured to receive the information from the third device viathe second antenna.
 3. Implantable battery device according to claim 2,wherein the processing unit transmits the information received via thesecond antenna from the second device to the first device via the firstantenna driven by the driving unit.
 4. Implantable battery deviceaccording to claim 2, wherein the processing unit is configured totransmit information to the third device via the second antenna. 5.Implantable battery device according to claim 1, wherein the drivingunit is configured to control an amplitude of an electromagnetic fieldemitted from the first antenna according to control signals receivedfrom the processing unit.
 6. Implantable battery device according toclaim 1, wherein the driving unit is configured to modulate theamplitude and/or a frequency of the electromagnetic field emitted fromthe first antenna according to the information received from theprocessing unit.
 7. Implantable battery device according to claim 1,wherein the processing unit is configured to obtain a charge state ofthe battery, and to control the inductive supply of energy to the firstdevice depending on the charge state.
 8. Implantable battery deviceaccording to claim 1, wherein the first antenna comprises a magneticallyinteracting part in a center of the first antenna for alignment of thefirst antenna with at least one other antenna.
 9. Implantable batterydevice according to claim 1, wherein the processing unit is configuredto control the inductive supply of energy to the first device dependingon information received by the third device.
 10. Implantable batterydevice according to claim 1, wherein the battery is recharged by theenergy received from the second device and inductively supplied to thebattery via the first antenna.
 11. Implantable battery device accordingto claim 1, wherein the first device is a cochlear implant, and thethird device is a hearing aid sound processor.
 12. Implantable batterydevice according to claim 9, wherein the processing unit is configuredto process information from the hearing aid sound processor to betransmitted to the cochlear implant.